Flow rate monitor for fluid cooled microwave ablation probe

ABSTRACT

A microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue and a coolant source operably coupled to the power source and configured to selectively provide fluid to the antenna assembly via a fluid path. The system also includes a controller operably coupled to the power source and a sensor operably coupled to the fluid path and the controller. The sensor is configured to detect fluid flow through the fluid path and the controller is configured to control the energy source based on the detected fluid flow.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a continuation application of U.S. patent application Ser. No. 15/188,373, filed on Jun. 21, 2016, which is a continuation application of U.S. patent application Ser. No. 14/054,434, filed on Oct. 15, 2013, now U.S. Pat. No. 9,370,399, which is a divisional application of U.S. patent application Ser. No. 12/568,972, filed on Sep. 29, 2009, now U.S. Pat. No. 8,556,889. The entire contents of each the foregoing applications are incorporated by reference herein.

BACKGROUND

1. Technical Field

The present disclosure relates generally to microwave ablation procedures that utilize microwave surgical devices having a microwave antenna that may be inserted directly into tissue for diagnosis and treatment of diseases. More particularly, the present disclosure is directed to a system and method for monitoring correct system operation of a microwave ablation system.

2. Background of Related Art

In the treatment of diseases such as cancer, certain types of cancer cells have been found to denature at elevated temperatures (which are slightly lower than temperatures normally injurious to healthy cells.) These types of treatments, known generally as hyperthermia therapy, typically utilize electromagnetic radiation to heat diseased cells to temperatures above 41° C., while maintaining adjacent healthy cells at lower temperatures where irreversible cell destruction will not occur. Other procedures utilizing electromagnetic radiation to heat tissue also include ablation and coagulation of the tissue. Such microwave ablation procedures, e.g., such as those performed for menorrhagia, are typically done to ablate and coagulate the targeted tissue to denature or kill the tissue. Many procedures and types of devices utilizing electromagnetic radiation therapy are known in the art. Such microwave therapy is typically used in the treatment of tissue and organs such as the prostate, heart, liver, lung, kidney, and breast.

One non-invasive procedure generally involves the treatment of tissue (e.g., a tumor) underlying the skin via the use of microwave energy. The microwave energy is able to non-invasively penetrate the skin to reach the underlying tissue. However, this non-invasive procedure may result in the unwanted heating of healthy tissue. Thus, the non-invasive use of microwave energy requires a great deal of control.

Presently, there are several types of microwave probes in use, e.g., monopole, dipole, and helical. One type is a monopole antenna probe, which consists of a single, elongated microwave conductor exposed at the end of the probe. The probe is typically surrounded by a dielectric sleeve. The second type of microwave probe commonly used is a dipole antenna, which consists of a coaxial construction having an inner conductor and an outer conductor with a dielectric junction separating a portion of the inner conductor. The inner conductor may be coupled to a portion corresponding to a first dipole radiating portion, and a portion of the outer conductor may be coupled to a second dipole radiating portion. The dipole radiating portions may be configured such that one radiating portion is located proximally of the dielectric junction, and the other portion is located distally of the dielectric junction. In the monopole and dipole antenna probe, microwave energy generally radiates perpendicularly from the axis of the conductor.

The typical microwave antenna has a long, thin inner conductor that extends along the axis of the probe and is surrounded by a dielectric material and is further surrounded by an outer conductor around the dielectric material such that the outer conductor also extends along the axis of the probe. In another variation of the probe that provides for effective outward radiation of energy or heating, a portion or portions of the outer conductor can be selectively removed. This type of construction is typically referred to as a “leaky waveguide” or “leaky coaxial” antenna. Another variation on the microwave probe involves having the tip formed in a uniform spiral pattern, such as a helix, to provide the necessary configuration for effective radiation. This variation can be used to direct energy in a particular direction, e.g., perpendicular to the axis, in a forward direction (i.e., towards the distal end of the antenna), or combinations thereof.

Invasive procedures and devices have been developed in which a microwave antenna probe may be either inserted directly into a point of treatment via a normal body orifice or percutaneously inserted. Such invasive procedures and devices potentially provide better temperature control of the tissue being treated. Because of the small difference between the temperature required for denaturing malignant cells and the temperature injurious to healthy cells, a known heating pattern and predictable temperature control is important so that heating is confined to the tissue to be treated. For instance, hyperthermia treatment at the threshold temperature of about 41.5° C. generally has little effect on most malignant growth of cells. However, at slightly elevated temperatures above the approximate range of 43° C. to 45° C., thermal damage to most types of normal cells is routinely observed. Accordingly, great care must be taken not to exceed these temperatures in healthy tissue.

In the case of tissue ablation, a high radio frequency electrical current in the range of about 500 mHz to about 10 gHz is applied to a targeted tissue site to create an ablation volume, which may have a particular size and shape. Ablation volume is correlated to antenna design, antenna performance, antenna impedance, and tissue impedance. The particular type of tissue ablation procedure may dictate a particular ablation volume in order to achieve a desired surgical outcome. By way of example, and without limitation, a spinal ablation procedure may call for a longer, narrower ablation volume, whereas in a prostate ablation procedure, a more spherical ablation volume may be required.

Microwave ablation devices utilize sensors to determine if the system is working properly. However, without delivery of microwave energy, the sensors may indicate that the probe assembly status is normal. Further, defects in antenna assemblies may not be apparent except at high powers. As such, when microwave ablation system is tested using a low power routine a post manufacture defect may not be apparent. This is especially important for high power microwave ablation devices, where failures may result in extremely high temperatures.

Fluid cooled or dielectrically buffered microwave ablation devices may also be used in ablation procedures to cool the microwave ablation probe. Cooling the ablation probe may enhance the overall ablation pattern of antenna, prevent damage to the antenna and prevent harm to the clinician or patient. However, during operation of the microwave ablation device, if the flow of coolant or buffering fluid is interrupted, the microwave ablation device may exhibit rapid failures due to the heat generated from the increased reflected power.

SUMMARY

According to an embodiment of the present disclosure, a microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue and a coolant source operably coupled to the power source and configured to selectively provide fluid to the antenna assembly via a fluid path. The system also includes a controller operably coupled to the power source and a sensor operably coupled to the fluid path and the controller. The sensor is configured to detect fluid flow through the fluid path and the controller is configured to control the energy source based on the detected fluid flow.

According to another embodiment of the present disclosure, a microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue and a coolant source operably coupled to the power source and configured to selectively provide fluid to the antenna assembly via a fluid path. The system also includes a controller operably coupled to the power source and a capacitive device operably coupled to the fluid path and the controller. The capacitive device is configured to detect fluid flow through the fluid path based on a capacitance of the capacitive device. The controller is configured to control the energy source based on the detected fluid flow.

According to another embodiment of the present disclosure, a method of detecting fluid flow through a microwave ablation system includes the steps of delivering microwave energy from a power source to tissue via an antenna assembly and supplying fluid from a coolant source to the antenna assembly via a fluid path. The method also includes the steps of detecting a capacitance of a capacitive device operably coupled to the fluid path and comparing the detected capacitance to a predetermined range. The method also includes the step of modifying output of energy from the energy source based on the comparison between the detected capacitance and the predetermined range.

According to another embodiment of the present disclosure, a microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue and a coolant source operably coupled to the power source and configured to selectively provide fluid to the antenna assembly via a fluid path. The system also includes a controller operably coupled to the power source and a sensor disposed within the fluid path and operably coupled to the controller. The sensor is configured to detect fluid flow through the fluid path. The controller is configured to control the generator based on the detected fluid flow.

According to another embodiment of the present disclosure, a microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue and a coolant source operably coupled to the power source and configured to selectively provide fluid to the antenna assembly via a fluid path. The system also includes a controller operably coupled to the power source and an electro-mechanical switch disposed within the fluid path and operably coupled to the controller. The electro-mechanical switch is configured to detect fluid flow through the fluid path based on movement of the switch between an open position and a closed position. The controller is configured to control the generator based on the detected fluid flow.

According to another embodiment of the present disclosure, a method of detecting fluid flow through a microwave ablation system includes the steps of delivering microwave energy from a power source to tissue via an antenna assembly and supplying fluid from a coolant source to the antenna assembly via a fluid path. The method also includes detecting a position of an electro-mechanical switch disposed within the fluid path and modifying output of energy from the energy source based on the detected position.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other aspects, features, and advantages of the present disclosure will become more apparent in light of the following detailed description when taken in conjunction with the accompanying drawings in which:

FIG. 1 shows a diagram of a microwave antenna assembly in accordance with an embodiment of the present disclosure;

FIG. 2 shows a perspective view of a distal end of the microwave antenna assembly of FIG. 1;

FIG. 3 shows a system block diagram of a microwave antenna assembly according to another embodiment of the present disclosure;

FIG. 4 shows the area of detail of FIG. 3 according to an embodiment of the present disclosure;

FIGS. 5A and 5B show the area of detail of FIG. 3 according to another embodiment of the present disclosure;

FIGS. 6A and 6B show the area of detail of FIG. 3 according to yet another embodiment of the present disclosure; and

FIG. 7 shows a system block diagram of a signal processing circuit according to an embodiment of the present disclosure.

DETAILED DESCRIPTION

Embodiments of the presently disclosed apparatus are described in detail below with reference to the drawings wherein like reference numerals identify similar or identical elements in each of the several views. In the discussion that follows, the term “proximal” will refer to the portion of a structure that is closer to a user, while the term “distal” will refer to the portion of the structure that is farther from the user.

Generally, the present disclosure is directed to a microwave antenna assembly having an energy source or generator adapted to deliver energy to tissue via the antenna assembly and a coolant source for circulating a dielectric coolant fluid through the microwave antenna assembly. More particularly, the present disclosure is directed to monitoring fluid flow through the microwave antenna assembly and controlling the energy source output based on the monitored fluid flow to prevent damage to the antenna and/or harm to the clinician or patient caused by overheating of the antenna assembly.

FIG. 1 shows a microwave ablation system 10 that includes a microwave antenna assembly 12 coupled to a microwave generator 14 via a flexible coaxial cable 16. The generator 14 is configured to provide microwave energy at an operational frequency from about 500 MHz to about 5000 MHz, although other suitable frequencies are also contemplated.

In the illustrated embodiment, the antenna assembly 12 includes a radiating portion 18 connected by feedline 20 (or shaft) to the cable 16. More specifically, the antenna assembly 12 is coupled to the cable 16 through a connection hub 22 having an outlet fluid port 30 and an inlet fluid port 32 that are connected in fluid communication with a sheath 38. The sheath 38 encloses radiating portion 18 and feedline 20 to form a chamber 89 (FIG. 2) allowing a coolant fluid 37 to circulate from ports 30 and 32 around the antenna assembly 12. The ports 30 and 32 are also coupled to a supply pump 34 that is, in turn, coupled to a supply tank 36 via supply line 86. The supply pump 34 may be a peristaltic pump or any other suitable type. The supply tank 36 stores the coolant fluid 37 and, in one embodiment, may maintain the fluid at a predetermined temperature. More specifically, the supply tank 36 may include a coolant unit that cools the returning liquid from the antenna assembly 12. In another embodiment, the coolant fluid 37 may be a gas and/or a mixture of fluid and gas.

FIG. 2 illustrates the radiating portion 18 of the antenna assembly 12 having a dipole antenna 40. The dipole antenna 40 is coupled to the feedline 20 that electrically connects antenna assembly 12 to the generator 14. The dipole antenna 40 includes a proximal portion 42 and a distal portion 44 interconnected at a feed point 46. The distal portion 44 and the proximal portion 42 may be either balanced (e.g., of equal lengths) or unbalanced (e.g., of unequal lengths). A dipole feed gap “G” is disposed between the proximal and distal portions 42 and 44 at the feed point 46. The gap “G” may be from about 1 mm to about 3 mm. In one embodiment, the gap “G” may be thereafter filled with a dielectric material at the feed point 46. The dielectric material may be polytetrafluoroethylene (PTFE), such as Teflon® sold by DuPont of Willmington, Del. In another embodiment, the gap “G” may be coated with a dielectric seal coating.

With reference to FIG. 2, the antenna assembly 12 also includes a choke 60 disposed around the feedline 20. The choke 60 may be a quarter-wavelength shorted choke that is shorted to the feedline 20 at the proximal end (not illustrated) of the choke 60 by soldering or other suitable methods.

Assembly 12 also includes a tip 48 having a tapered end 24 that terminates, in one embodiment, at a pointed end 26 to allow for insertion into tissue with minimal resistance at a distal end of the radiating portion 18. In those cases where the radiating portion 18 is inserted into a pre-existing opening, tip 48 may be rounded or flat. The tip 48 may be formed from a variety of heat-resistant materials suitable for penetrating tissue, such as metals (e.g., stainless steel) and various thermoplastic materials, such as poletherimide, and polyamide thermoplastic resins.

With reference to FIG. 3, a microwave ablation system, shown generally as 200, according to an embodiment of the present disclosure is depicted. The system 200 includes an ablation device 202 having an antenna 203 and a handle 205 used to ablate tissue. A generator 206, which is substantially similar to power generating source 28, supplies the ablation device 202 with energy via coaxial cable 204. Ablation device is supplied with coolant or fluid from coolant supply 210 through conduit 208. The coolant flows through the ablation device 202 as described above and exits the ablation device via conduit 208 into chamber 214. Conduit 208 may be a multi-lumen conduit having an inflow lumen for supplying the ablation device 202 with coolant and an outflow lumen for coolant to exit the ablation device 202 into the chamber 214. Additionally, conduit 208 may be provided as two separate conduits, an inflow conduit and an outflow conduit.

As shown in FIG. 3, a sensor 212 is provided to monitor the flow rate of fluid through conduit 208. As described above, when coolant circulation is interrupted, the ablation device tends to exhibit rapid failures. Further, when coolant circulation is too great and/or the flow rate of fluid through conduit 208 exceeds a predetermined threshold maximum (e.g., 100 ml/min, 130 ml/min, etc.), the ablation device may be exhibiting symptoms of a fluid leak. By monitoring the fluid flow through microwave ablation system 200, damage to the ablation device as well as harm to the clinician or patient may be prevented. Controller 216 is coupled to generator 206 and is configured to control generator 206 based on an input or signal from sensor 212. Controller 216 may be a microprocessor or any logic circuit able to receive an input or signal from sensor 212 and provide an output to control generator 206. Controller 216 may be operably coupled to a storage device or memory (not shown) configured to store programmable instructions, historical data, lookup tables, operating parameters, etc. Sensor 212 may be a single sensor or an array of sensors configured to detect operational parameters of the ablation device 202 in order to determine if the microwave ablation system 200 is functioning properly. In use, sensor 212 provides an electrical signal to the controller 216 that represents a real-time measurement or indication such as fluid flow, pressure, capacitance, etc., as described in further detail below. Controller 216 compares the electrical signal to a predetermined range. If the electrical signal is within a predetermined range, the controller 216 controls the generator 206 to continue with the ablation procedure. If the electrical signal is outside the predetermined range, the controller 216 controls the generator 206 to cease the ablation procedure and/or modify generator 206 output. For example, the predetermined range may be a range of fluid flow rates through conduit 208. In one embodiment, the predetermined range of flow rate requirements is between about 70 ml/min and about 130 ml/min. In this scenario, an operating range of flow rates may be between about 100 ml/min and about 120 ml/min. In another embodiment, the predetermined range of flow rate requirements is between about 40 ml/min and about 100 ml/min. In this scenario, an operating range of flow rates may be between about 60 ml/min and about 80 ml/min.

Sensor 212 may be incorporated into ablation device 202 or controller 216 may be coupled to ablation device 202 and/or controller 216. Sensor 212 may be placed anywhere along the fluid path. For instance, sensor 212 may be placed in antenna 203, handle 205 or along the inflow lumen or outflow lumen of conduit 208. The sampling rate of sensor 212 is sufficient to detect intermittent problems with the flow of fluid through the ablation system 200. The sensor 212 is configured to detect fluid flow during startup before microwave energy is delivered to the ablation device 202 or during an ablation procedure.

With reference to FIG. 4, a sensor 312 according to another embodiment of the present disclosure is shown operably coupled to conduit 208. Sensor 312 is configured to operate in conjunction with microwave ablation system 200 as substantially described above with reference to sensor 212. Sensor 312 is a parallel plate capacitor 314 including capacitive plates 322 and 324 disposed about conduit 208. More specifically, conduit 208 and its contents (e.g., fluid, air, air bubbles, etc.) are disposed between capacitive plates 322 and 324 to operate as a dielectric of capacitor 314. Capacitive plates 322 and 324 may be disposed about the inflow lumen of conduit 208, the outflow lumen of conduit 208, or both the inflow and outflow lumens of conduit 208. Capacitance of capacitor 314 is calculated using the following formula (1):

C=ε*A/d   (1)

Applying equation (1) to the embodiment illustrated in FIG. 4, C is the capacitance of capacitor 314, A is the area of capacitive plates 322 and 324, d is the distance between capacitive plates 322 and 324, and ε is the permittivity of the dielectric between capacitive plates 322 and 324 (e.g., conduit 208 and its contents). Given a constant area A of capacitive plates 322, 324 and a constant distance d between capacitive plates 322, 324, any change in permittivity ε of the dielectric between capacitive plates 322, 324, namely conduit 208 and its contents, causes a change in conductivity of capacitor 314. For example, if fluid flow through conduit 208 is interrupted resulting in the presence of air, air bubbles, and/or a lack of fluid flow through a portion of conduit 208 disposed between capacitive plates 322, 324, the ability of conduit 208 and its contents to transmit an electric field decreases, i.e., the permittivity ε of conduit 208 and its contents decreases, resulting in a decrease in conductivity C of capacitor 314. That is, the presence of air within conduit 208, rather than fluid, effectively decreases the permittivity ε of the dielectric between capacitive plates 322, 324 since the dielectric constant (or permittivity) of the fluid (e.g., water) is significantly higher than air.

Sensor 312 provides an electrical signal to the controller 216 indicating the capacitance C of capacitor 314 and/or the change in capacitance C of capacitor 314. Controller 216 compares the electrical signal to a predetermined range. If the electrical signal is within the predetermined range, the controller 216 controls the generator 206 to continue with the ablation procedure. If the electrical signal is outside the predetermined range, the controller 216 controls the generator to terminate the ablation procedure and/or modify generator 206 output.

In another embodiment, sensor 312 may be disposed about the outflow lumen of conduit 208 to detect changes in capacitance C of capacitor 314 due to steam caused by overheating of ablation device 202. In this scenario, the presence of steam in conduit 208 changes the permittivity ε of the dielectric between capacitive plates 322, 324, thereby changing the capacitance C of capacitor 314.

Referring now to FIGS. 5A and 5B, a sensor 412 according to another embodiment of the present disclosure is shown operably coupled to conduit 208. Sensor 412 is configured to operate in conjunction with microwave ablation system 200 as substantially described above with reference to sensor 212. Sensor 412 includes an electro-mechanical switch 420 disposed in the fluid path through conduit 208. Switch 420 may be disposed within the inflow lumen of conduit 208, within the outflow lumen of conduit 208, or within both the inflow and outflow lumens of conduit 208. Switch 420 operates to open or close an electrical circuit electrically connected to controller 216 depending on fluid flow through conduit 208. More specifically, switch 420 is hinged at one end to a pivot 414 disposed on an inner surface of conduit 208 and is configured at an opposing end to movably engage a contact 416 disposed on an opposing inner surface of conduit 208 upon pivotal movement about pivot 414 to close an electrical circuit between sensor 412 and controller 216. In the illustrated embodiment, switch 420 is naturally biased in the open position by pivot 414.

As best shown in FIG. 5A, sufficient fluid flow through conduit 208 (e.g., 70 ml/min≦fluid flow rate≦130 ml/min), as depicted by directional arrows illustrated within conduit 208, biases switch 420 to the closed position, thereby closing the electrical circuit between sensor 412 and controller 216. The closed electrical circuit indicates to the controller 216 that sufficient fluid flow exists through conduit 208. As best shown in FIG. 5B, insufficient fluid flow through conduit 208 allows switch 420 to return to its naturally biased open position, thereby opening the electrical circuit between sensor 412 and controller 216. The open electrical circuit indicates to the controller 216 that insufficient fluid flow (e.g., fluid flow rate<70 ml/min) exists through conduit 208. As such, if switch 420 is in the closed position, i.e., contact 416 is engaged by switch 420, the controller 216 controls the generator 206 to continue with the ablation procedure. If switch 420 is in the open position, i.e., switch 420 is disengaged from contact 416, the controller 216 controls the generator to terminate the ablation procedure and/or modify generator 206 output. Sufficient fluid flow and/or insufficient fluid flow may be dictated by a predetermined range of flow rate requirements depending on the ablation device 202 used.

Referring now to FIGS. 6A and 6B, a sensor 512 according to another embodiment of the present disclosure is shown operably coupled to conduit 208. Sensor 512 is configured to operate in conjunction with microwave ablation system 200 as substantially described above with reference to sensor 212. Sensor 512 includes an electro-mechanical switch 520 disposed in the fluid path through conduit 208. Switch 520 may be disposed within the inflow lumen of conduit 208, within the outflow lumen of conduit 208, or within both the inflow and outflow lumens of conduit 208. Switch 520 operates to open or close an electrical circuit electrically connected between sensor 512 and controller 216 depending on fluid flow through conduit 208. More specifically, switch 520 is hinged at one end to a pivot 514 disposed on an inner surface of conduit 208 and is configured at an opposing end to movably engage a contact 516 disposed on an opposing inner surface of conduit 208 upon pivotal movement about pivot 514 to close an electrical circuit between sensor 512 and controller 216. In the illustrated embodiment, switch 520 is naturally biased in the closed position by pivot 514.

As best shown in FIG. 6A, sufficient fluid flow through conduit 208 (e.g., 40 ml/min≦fluid flow rate≦100 ml/min), as indicated by directional arrows through conduit 208, biases switch 520 to the open position, thereby opening the electrical circuit between sensor 512 and controller 216. The open electrical circuit indicates to the controller 216 that sufficient fluid flow exists through conduit 208. As best shown in FIG. 6B, insufficient fluid flow through conduit 208 allows switch 520 to return to its naturally biased closed position, thereby closing the electrical circuit between sensor 512 and controller 216. The closed electrical circuit indicates to the controller 216 that insufficient fluid flow (e.g., fluid flow rate<40 ml/min) exists through conduit 208. As such, if switch 520 is in the open position, i.e., switch 520 is disengaged from contact 516, the controller 216 controls the generator 206 to continue with the ablation procedure. If switch 520 is in the closed position, i.e., contact 516 is engaged by switch 520, the controller 216 controls the generator to terminate the ablation procedure and/or modify generator 206 output.

Referring to the illustrated embodiments of FIGS. 5A, 5B, 6A, and 6B, the circuitry connecting sensor 412 and/or 512 to the controller 216 for purposes of switch state detection may include a resistor (not shown) in series with switch 420, 520. In this scenario, the total series resistance of the switch 420, 520 and in-line resistor may be monitored by the controller 216 to control generator 206 output.

With reference to FIG. 7, a signal processing circuit 300 may be incorporated within microwave ablation system 200 and electrically connected between sensor 212, 312, 412, 512 and controller 216. Circuit 300 processes electrical signals sent from sensor 212, 312, 412, 512 to controller 216 for the purpose of controlling generator 206 output, as described above with respect to FIGS. 4, 5A, 5B, 6A, and 6D.

More specifically, circuit 300 includes an amplifier 220 incorporating the sensor 212, 312, 412, 512 in a resonant feedback loop. Amplifier 220 may be, for example, a Hartley Oscillator including a tuning capacitor in parallel with two inductors in series. In embodiments incorporating sensor 312, capacitor 314 may operate as the tuning capacitor. In embodiments incorporating sensors 212, 412, or 512, a tuning capacitor electrically connected in series with sensor 212, 412, 512 may be added to amplifier 220.

The output of amplifier 220 is fed into a band pass filter 222 centered on the resonant frequency consistent with fluid flow through conduit 208. That is, in the embodiment of FIG. 4, filter 222 is centered on the resonant frequency consistent with fluid flow within conduit 208 between capacitive plates 322, 324. In the embodiments of FIGS. 5A, 5B, 6A, and 6B, filter 222 is centered on the resonant frequency consistent with fluid flow through switch 420 (FIGS. 5A and 5B) or switch 520 (FIGS. 6A and 6B).

A sample-and-hold peak detector circuit 224 is operably coupled to the filter 222 output such that filter 222 output is sampled and held steady by circuit 224. Circuit 224 samples filter 222 output at a rate sufficient to detect intermittent interruptions of fluid flow through conduit 208 and/or the presence of small air bubbles in conduit 208. In the embodiment of FIG. 4, absence of a peak in the filter 222 output as detected by circuit 224 indicates air (or air bubbles) passing through conduit 208 at capacitive plates 322, 324, as described above with respect to FIG. 4. In the embodiments of FIGS. 5A, 5B, 6A, and 6D, a peak in the filter 222 output as detected by circuit 224 indicates the position of switch 420 (FIGS. 5A and 5B) or switch 520 (FIGS. 6A and 6B) and/or fluid flow through conduit 208 as being sufficient or insufficient, as described above with respect to FIGS. 5A, 5B, 6A, and 6D.

The described embodiments of the present disclosure are intended to be illustrative rather than restrictive, and are not intended to represent every embodiment of the present disclosure. Various modifications and variations can be made without departing from the spirit or scope of the disclosure as set forth in the following claims both literally and in equivalents recognized in law. 

1-20. (canceled)
 21. An electrosurgical system, comprising: an electrosurgical instrument configured to deliver electrosurgical energy to tissue; a coolant source operably coupled to the electrosurgical instrument via a fluid conduit, the coolant source configured to supply a fluid to the electrosurgical instrument through the fluid conduit; a sensor operatively coupled to the fluid conduit, the sensor configured to sense a flow of the fluid through the fluid conduit and to generate a signal indicative of the flow of the fluid; and a controller operably coupled to the sensor, the controller configured to: receive the signal indicative of the flow of the fluid from the sensor; and detect at least one variation of the signal to detect an interruption in the flow of the fluid.
 22. The electrosurgical system according to claim 21, further comprising a power source coupled to the electrosurgical instrument, the controller configured to control the power source based on the flow of the fluid.
 23. The electrosurgical system according to claim 21, further comprising an amplifier operably coupled to the controller, the amplifier configured to amplify the signal.
 24. The electrosurgical system according to claim 23, wherein the sensor is disposed in a resonant feedback loop with the amplifier.
 25. The electrosurgical system according to claim 21, wherein the sensor is a capacitive device disposed about the fluid conduit, the capacitive device configured to sense a capacitance of the fluid.
 26. The electrosurgical system according to claim 25, wherein the capacitive device includes a pair of parallel capacitive plates and a dielectric disposed therebetween.
 27. The electrosurgical system according to claim 21, wherein the sensor is an electro-mechanical switch operably coupled to the fluid conduit, the electro-mechanical switch configured to be deflected by the flow of the fluid.
 28. The electrosurgical system according to claim 27, wherein the electro-mechanical switch is disposed within the fluid conduit.
 29. The electrosurgical system according to claim 21, wherein the fluid conduit includes an inflow lumen and an outflow lumen.
 30. An electrosurgical system, comprising: a power source; an electrosurgical instrument configured to couple to the power source and configured to deliver electrosurgical energy from the power source to tissue; a coolant source operably coupled to the electrosurgical instrument via a fluid conduit, the coolant source configured to supply a fluid to the electrosurgical instrument through the fluid conduit; a sensor operatively coupled to the fluid conduit, the sensor configured to sense a flow of the fluid through the fluid conduit and generate a signal indicative of the flow of the fluid; an amplifier coupled to the sensor and configured to generate an amplified signal; a bandpass filter coupled to the amplifier and configured to filter the amplified signal, the bandpass filter being centered on a resonant frequency consistent with fluid flow through the fluid conduit; and a controller operably coupled to the amplifier and the power source, the controller configured to modify output of energy from the power source based on the amplified signal.
 31. The electrosurgical system according to claim 30, wherein the sensor is a capacitive device disposed about the fluid conduit, the capacitive device configured to sense a capacitance of the fluid.
 32. The electrosurgical system according to claim 31, wherein the capacitive device includes a pair of parallel capacitive plates and a dielectric disposed therebetween.
 33. The electrosurgical system according to claim 31, wherein the controller is configured to compare the capacitance to a predetermined range.
 34. The electrosurgical system according to claim 33, wherein the controller is configured to modify output of energy from the power source based on the comparison of the capacitance to the predetermined range.
 35. The electrosurgical system according to claim 30, wherein the sensor is an electro-mechanical switch operably coupled to the fluid conduit, the electro-mechanical switch configured to be deflected by the flow of the fluid.
 36. The electrosurgical system according to claim 35, wherein the electro-mechanical switch is disposed within the fluid conduit.
 37. The electrosurgical system according to claim 30, wherein the controller is configured to detect an interruption in the flow of the fluid.
 38. The electrosurgical system according to claim 30, wherein the controller is configured to detect at least one peak in the signal.
 39. The electrosurgical system according to claim 30, wherein the fluid conduit includes an inflow lumen and an outflow lumen. 